Methods and systems for providing a power signal to an implantable device

ABSTRACT

A push-pull amplifier efficiency provides a 4:1 (12 dB) course adjustment of power output by using a single digital control input. The amplifier is provided with an input voltage (VDD) having sixteen steps ranging from 1.25 volts to 3.00 volts. Based on the digital control, an integrated circuit switches between a high power mode and a low power mode. In the low power mode, the output voltage is equivalent to the input voltage. In the high power mode, the amplifier provides an output of twice the input voltage (or four times the power).

RELATED APPLICATIONS

The present application is a divisional application of U.S. applicationSer. No. 10/209,054, filed Jul. 31, 2002 now U.S. Pat. No. 7,016,738,which application is incorporated herein by reference in its entirety.

BACKGROUND

The present invention relates to battery powered implantable devices,and in particular to an improved Radio Frequency (RF) power amplifierfor Implantable Cochlear Stimulator (ICS) systems. Such ICS systemsprovide improved hearing for the hearing impaired. The RF poweramplifier serves the important function of providing power to theimplanted part of the ICS system and the efficiency of the RF poweramplifier is crucial in developing the miniaturized systems of thefuture.

U.S. Pat. No. 4,400,590 issued Aug. 23, 1983 for “Apparatus forMulti-Channel Cochlear Implant Hearing Aid System” describes andillustrates a system for electrically stimulating predeterminedlocations of the auditory nerve within the cochlea of the ear, whichsystem includes a multi-channel intra-cochlear electrode arraypositioned adjacent to the auditory nerve within the cochlea of the ear.The electrode array comprises a plurality of exposed electrode pairsspaced along and embedded in a resilient curved base for implantation inaccordance with the method of surgical implantation described in U.S.Pat. No. 3,751,605 issued Aug. 7, 1973 for “Method of Inducing Hearing.”The hearing aid system described in the '590 patent includes a signalprocessor located outside the body of a hearing impaired patient. Thesignal processor receives audio signals (i.e., sound waves) and convertsthe audio signals into analog data signals which are carried by a leadthrough the patient's skin to the implantable multi-channelintra-cochlear electrode array. The analog signals are applied toselected ones of the plurality of exposed electrode pairs included inthe intra-cochlear electrode array to electrically stimulatepredetermined locations of the auditory nerve.

U.S. Pat. No. 4,532,930, issued Aug. 6, 1985 for “Cochlear ImplantSystem For an Auditory Prosthesis” describes and illustrates a multipleelectrode system which does not employ a lead passing through the skin.Though multiple electrodes are employed to stimulate hearing, the systemonly operates with a single pulsatile output stimulating a singleelectrode channel at any given time. Such a sequential system is limitedin speed of operation, and does not provide for analog operation wherecontinuous stimulating signals, controllable in amplitude, aresimultaneously applied to a number of electrode channels. Further, thesystem is subject to charge imbalance with misprogramming or circuitfault and inefficient use of electrical power. Moreover, once thestimulator unit is implanted there are no means for monitoring itsongoing circuit operation or power requirements so as to optimize itscontinued operation.

U.S. Pat. No. 4,592,359, issued Jun. 3, 1986 for “Multi-ChannelImplantable Neural Stimulator” describes a cochlear implant systemhaving 4 current sources and 4 current sinks per channel, controlled byseries switches, to provide 16 different circuits for supplying 16levels of 2 polarities to each output channel. In a pulsatile mode, thesystem provides for simultaneous update (amplitude control) and outputto all channels. However, the system does not permit simultaneous analogupdate and output on all channels and the electrode pairs for eachchannel are not electrically isolated from all other electrode pairswhereby undesired current leakage may occur. Further, once thestimulator is implanted there are no means for monitoring its ongoingcircuit operation or power requirements so as to optimize its continuedoperation.

U.S. Pat. No. 4,947,844, issued Aug. 14, 1990 for “Receiver/StimulatorFor Hearing Prosthesis” describes and illustrates a multiple channelelectrode system. The system includes an implantable receiver/stimulatorconnected to an implantable electrode array. Included in the implantablereceiver/stimulator is a transmitter for telemetering one electrodevoltage, measured during stimulation, to an external receiver formonitoring and analysis as an indicator of proper operation of theimplantable stimulator. The transmitter comprises an oscillatoroperating at a frequency of about 1 MHz. The output of the oscillator iscoupled to the implant's receiving coil. The oscillator signal, whenreceived after transmission, is demodulated to recover the selectedvoltage waveforms.

Recently, ICS systems have been introduced which include abehind-the-ear speech processor, e.g., of the type described in U.S.Pat. No. 5,824,022 issued Oct. 20, 1998 for ‘Cochlear Stimulation SystemEmploying Behind-The-Ear (BTE) Speech Processor with Remote Control.’BTE speech processors offer several advantages, but because of theirsmall size, BTE speech processors are limited in the size of the batterythey may carry (which in turn limits the useful life of the battery.)The small battery size results in a requirement for very low powerconsumption. Further, known BTE external devices may be required tocooperate with two or more varieties of implantable devices. Suchvarieties of implantable devices have significantly different powerrequirements, and techniques such as dynamic output power control havebeen used to meet the varying power requirements. Unfortunately, knownmethods of dynamic output power control fail to produce consistentvoltage output when required to operate over a wide range of voltages.Specifically, the threshold voltage of amplifiers with MOS transistorsmay limit the minimum voltage the amplifier can produce with adequateoutput voltage control.

What is needed in an RF amplifier with a wide dynamic range, suitablefor use in an ICS system.

SUMMARY

The present invention addresses the above and other needs by providingan RF amplifier with a 4:1 (12 dB) course adjustment of power output,which course adjustment is controlled by a single digital control input.The RF amplifier is provided with an input voltage (V_(DD)) havingsixteen steps ranging from 1.25 volts to 3.00 volts. Based on thedigital control, an integrated circuit switches between a high powermode and a low power mode. In the low power mode, the output voltage isa modulated version of the input voltage. In the high power mode, theamplifier provides an output that is a modulated version of twice theinput voltage (or four times the power). The RF amplifier includes atransformer-coupled output-matching network. To operate in the low powermode, a first modulated signal is input to a first output driver, toproduce a first push-pull output between 0 and V_(DD), resulting in aV_(DD) voltage swing through a primary coil. To operate in the highpower mode, the first modulated signal is input to the first outputdriver, to produce the first push-pull output modulated between 0 andV_(DD), and a second modulated signal (a 180 degrees phase shiftedversion of the first modulated signal) is input to a second outputdriver, to produce an opposing second push-pull output modulated between0 and V_(DD), resulting in a 2 V_(DD) voltage swing through the primarycoil.

In accordance with one aspect of the invention, there is provided animproved RF amplifier for an Implantable Cochlear Stimulation (ICS)system that may be switched between a low power mode and a high powermode, to efficiently provide power to different implantable deviceshaving different power requirements. There is a desire to have a singleexternal device capable of interfacing with two or more electronicallydifferent implantable devices. In one example, a first implantabledevice has a power requirement range from 50 to 200 mW, and a secondimplantable device has a power requirement range from 10 to 90 mW. Knownmethods for controlling power over the range from 10 to 200 mW mayresult in a failure to provide an efficient output at very low powerlevels. The RF amplifier of the present invention provides a 4:1 courseadjustment of output power to meet the requirements of both a high powerrequirement implantable device, and a low power requirement implantabledevice, and thereby retains the ability to efficiently control the poweroutput at low power levels.

It is a further feature of the present invention to provide a 4:1 courseoutput power adjustment through digital control while avoiding acomplicated hardware solution. The RF amplifier of the present inventioncomprises a transformer-coupled output-matching network which may bedigitally switched between a high power push-pull configuration toobtain twice the supply voltage, and a low power mode operating at thesupply voltage.

BRIEF DESCRIPTION OF THE DRAWINGS

The above and other aspects, features and advantages of the presentinvention will be more apparent from the following more particulardescription thereof, presented in conjunction with the followingdrawings wherein:

FIG. 1 shows elements of an Implantable Cochlear Stimulation (ICS)system suitable for application of an RF amplifier according to thepresent invention;

FIG. 2 shows a digitally controlled amplifier providing a wide dynamicrange;

FIG. 3 depicts a first push-pull output, a second push-pull output, anda resulting primary (swing) voltage;

FIG. 4A shows an RF amplifier according to the present invention;

FIG. 4B shows an example of matching circuits suitable for use in the RFamplifier of FIG. 4A;

FIG. 5 depicts a carrier signal, a data signal, and a resultingmodulated signal;

FIG. 6A shows details of a first amplifier comprising in-seriesinvertors;

FIG. 6B shows details of a second amplifier comprising in-seriesinvertors; and

FIG. 7 depicts an invertor comprising PMOS and NMOS transistors.

Corresponding reference characters indicate corresponding componentsthroughout the several views of the drawings.

DETAILED DESCRIPTION

The following description is of the best mode presently contemplated forcarrying out the invention. This description is not to be taken in alimiting sense, but is made merely for the purpose of describing thegeneral principles of the invention. The scope of the invention shouldbe determined with reference to the claims.

Implantable Cochlear Stimulation (ICS) systems 10 have been developed toprovide the sensation of hearing to the hearing impaired. An exemplaryICS system 10 shown in FIG. 1 includes a microphone 12 for convertingacoustic energy into an electrical signal, a signal processor 16 forprocessing the electrical signal to generate a processed signal, amicrophone lead 14 for carrying the electrical signal from themicrophone 12 to the signal processor 16, a primary antenna 20 fortransmitting the processed signal over a Radio Frequency (RF) link 22, aprimary coil lead 18 for carrying the processed signal from the SignalProcessor 16 to the primary antenna 20, a secondary antenna 24 forreceiving the processed signal transmitted over the RF link 22, animplantable processor 28 for processing the received signal to generatea stimulation signal, a secondary coil lead 26 for carrying theprocessed signal from the secondary antenna 24 to the implantableprocessor 28, and an implantable electrode array 30 for providing thestimulation signal to nerves in the cochlea.

Some electrical devices require a power supply with wide dynamic range.A digitally controlled amplifier 32 with a course voltage adjustmentproviding a wide dynamic range is shown in FIG. 2. The amplifierreceives a DC power signal with voltage Vp, and produces a power outputat either Vp or twice Vp, thereby providing a 4:1 course poweradjustment. A periodic signal 34 is preferably a square wave betweenzero and Vs, or may be another waveform which sufficiently swings aboveand below the input thresholds of subsequent processing elements (e.g.,output drivers). The signal 34 is provided to a first output driver 50 aand to a Select Power Level and 180 Degree Phase Shift Processor(hereafter, level and phase processor) 44. A power level control signal42 is also provided to the level and phase processor 44. The signal 42indicates if the amplifier 32 is in a high power mode or in a low powermode. In the low power mode, the level and phase processor 44 generatesa phase shifted signal 38 set to zero. In the high power mode, the leveland phase processor 44 generates a phase shifted signal 38 set to thesignal 34 with a 180 degree phase shift. The signal 38 is provided to asecond output driver 50 b.

The first output driver 50 a generates a first push pull output 52 a byamplifying the signal 34 (i.e., generating an amplified replica of thesignal 34). The second output driver 50 b similarly generates a secondpush pull output 52 b by amplifying the signal 38 (i.e., generating anamplified replica of the signal 38). The push-pull signals 52 a and 52 bare connected through in-series primary coil L1 and first matchingnetwork 56 resulting in a primary voltage (also called swing voltage) 54across the coil L1. The coil L1 is inductively coupled with a secondarycoil L2 which is in-series with a second matching circuit 64. Asecondary voltage 62 is generated across the coil L2, and an outputsignal 66 is generated by the combination of the coil L2 and secondmatching circuit 64.

Plots of the first push-pull output 52 a, the second push-pull output 52b, and the resulting primary voltage 54 are shown in FIG. 3. In the highpower mode, the first push pull signal 52 a and the second push pullsignal 52 b combine to generate a voltage swing of twice Vp across theprimary coil L1 (FIG. 2). The coupling of the primary coil L1 with thesecondary coil L2 results in an output signal with voltage 2Vp in thehigh power mode. In the low power mode, the second push-pull output iszero (i.e., set to ground) and the primary voltage resembles the firstpush-pull output 52 a.

In known ICS systems 10 the processed signal may include both data andpower. A digitally controlled RF amplifier 32 a with wide dynamic rangeis shown in FIG. 4A. Such amplifier 32 a is suitable for use within thesignal processor 16 (FIG. 1) to help generate the processed signalprovided to the primary antenna 20 (FIG. 1). The amplifier 32 a receivesthree digital signals and DC power. In the RF amplifier 32 a, theperiodic signal 34 in FIG. 2 comprises a carrier signal 46 whichprovides a high frequency carrier for RF power transmission. A datasignal 36 (preferably 1 MHz) contains information that is transmitted bymodulation of the carrier signal 46. The carrier signal 46 and datasignal 36 are input to a first NAND 70 a where a first modulated signal40 a is generated by modulating the carrier signal 46 by the data signal36. The first modulated signal 40 a is provided to a first amplifier 72a, and to a second NAND 70 b. The power level control signal 42 is alsoprovided to the NAND 70 b. In the low power mode, a second modulatedsignal 40 b generated by the NAND 70 b is set to zero. In the high powermode, the second modulated signal 40 b is set to the first modulatedsignal 40 a with a 180 degree phase shift. The second modulated signal40 b is provided to a second amplifier 72 b. The amplifiers 72 a and 72b also receive a power signal 48 which preferably has 16 steps between1.25 and 3 volts. While the example in FIG. 4A utilizes NANDs, anysuitable logic circuit may be used.

Continuing with FIG. 4A, the first amplifier 72 a generates the firstpush pull output 52 a. The second amplifier 72 b generates a second pushpull output 52 b 180 degrees out of phase with the first push pulloutput 52 a when the power level control signal 42 is set to high power,and generates a zero output (i.e., is set to ground) when the powerlevel control signal 42 is set to low power. The first push-pull output52 a and second push-pull output 52 b are connected through the primarycoil 58 and a capacitor C1 (preferably 500 pF), wherein the capacitor C1performs as the first matching circuit 56 in FIG. 2. The primary coil L1is inductively coupled with the secondary coil L2. The secondary coil L2is connected to the antenna 20 through the second matching network 64.The ratio between the primary coil 58 and the secondary coil 60 may be1:1, 1:2, or some other ratio, based on the power requirements and thecomponent sizes of the amplifier 32 a.

When the power level control signal 42 is set to high power, the firstpush pull output 52 a and the second push pull output 52 b combine(i.e., are enabled) resulting in the primary voltage (i.e., swingvoltage) 54 present across the primary coil L1 which is twice thevoltage of the power signal 48. When the power level control signal isset to low power, the second push pull output 52 b is zero (i.e.,ground), and the amplitude of the primary voltage 54 present across theprimary coil L1 is equal to the voltage of the power signal 48. Thus,the amplifier 32 a provides a high power mode, and a low power mode,controlled by the digital power level control signal 42, wherein thehigh voltage mode results in twice the voltage across the primary coilL1 as the low voltage mode.

Examples of matching circuits 56 and 64 suitable for use in theamplifier 32 a described in FIG. 4A are shown in FIG. 4B. The matchingcircuits of FIG. 4B are matched to coils L1 and L2 of 200 nH with atransformer ratio of 0.9. The first matching circuit 56 may comprise acapacitor C1 (preferably 500 pF). The second matching circuit 64 maycomprise a circuit wherein the coil L2 is electrically connected betweena fourth node V4 and a node Vout. The node V4 is electrically connectedto ground. An inductor L3 (preferable 47 nH) is electrically connectedbetween the node Vout and a first node V1. A second capacitor C2(preferably 120 pF) is electrically connected between the node V1 andthe node V4. A capacitor C3 (preferably 56 pF) is electrically connectedbetween the node V1 and a second node V2. A fourth coil LA (preferably180 nH) and a fourth capacitor C4 (preferably 1200 pF) are electricallyconnected in series between the node V2 and the node V4. A fifthcapacitor C5 (preferably 56 pF) and a resister R (preferably 50 ohms),which resister R represents a load, are electrically connected in seriesbetween the node V2 and ground. Those skilled in the art will recognizethat other matching circuits may be substituted for the circuitsdescribed in FIG. 4B, and a wide dynamic range amplifier according tothe present invention, including a different matching circuit, isintended to come within the scope of the present invention.

The carrier signal 46, data signal 36, and first modulated signal 40 a(corresponding to the high power mode) are shown in FIG. 5. The carriersignal 46 is preferably a square wave, preferably between 20 Hz and 1000Ghz, and more preferably 49 MHz, and preferably has amplitude equal toV_(p), the voltage level of the power signal 48. The data signal 36 is adigital signal (i.e., is either zero or one), and is preferably at 1MHz. The first modulated signal 40 a is zero when the data signal 36 iszero, and is a copy of the carrier signal 46 elsewhere.

An example of the first amplifier 72 a is shown in FIG. 6A, and anexample of the second amplifier 72 b is shown in FIG. 6B. The amplifier72 a receives the first modulated signal 40 a as a control input, andthe power signal 48 as a power source. The amplifier 72 a comprises sixstages (or invertors INV_(an)) preferably comprising in-series invertorsINV_(a1), INV_(a2), INV_(a3), INV_(a4), INV_(a5), and INV_(a6), whereineach stage (after the first stage) receives the output of the previousstage as a control signal, and each stage receives the power signal 48as a power source. The power provided at the output of each stageincreases, and the output of the final stage (the first push-pull output52 a) provides the maximum designed power available from the powersignal 48. Similarly, the example of the second amplifier 72 b receivesthe second modulated signal 40 b and the power signal 48, and processesthe signals though six stages (or invertors INV_(bn)) preferablycomprising in-series invertors INV_(b1), INV_(b2), INV_(b3), INV_(b4),INV_(b5), and INV_(b6), to generate the second push-pull output 52 b.The number of stages may be varied as long as the resulting delays inthe first push-pull output 52 a and the second push-pull output 52 b aresubstantially identical (i.e., within the normal tolerances ofelectrical components), and typically the first amplifier 72 a and thesecond amplifier 72 b will achieve identical delays by having the samenumber of stages.

An example INV** of a single stage of either the amplifier 72 a or 72 bis shown in FIG. 7. The stage, INV_(an) or INV_(bn), comprises eightPMOS transistors PMOS₁, PMOS₂, PMOS₃, PMOS₄, PMOS₅, PMOS₆, PMOS₇, andPMOS₈, and eight NMOS transistors NMOS₁, NMOS₂, NMOS₃, NMOS₄, NMOS₅,NMOS₆, NMOS₇, and NMOS₈. An input I_(in) is a control signal for all ofthe switches in the stage. While the input I_(in) is positive, the PMOSswitches close, and the NMOS switches open, whereby the power signal 48is connected to an output I_(out). While the input I_(in) is zero, thePMOS switches open and the NMOS switches close, thereby connecting theoutput I_(out) to ground.

While the invention herein disclosed has been described by means ofspecific embodiments and applications thereof, numerous modificationsand variations could be made thereto by those skilled in the art withoutdeparting from the scope of the invention set forth in the claims.

1. A method of providing a power signal to an implantable device, saidmethod comprising: receiving, by a processor, a control signal thatselectively indicates one of a low power mode and a high power mode;receiving, by a first output driver, a first input signal andgenerating, by the first output driver, a first output signal based onthe first input signal; receiving, by a second output driver, a signaloutput by the processor and generating, by the second output driver, asecond output signal based on the signal output by the processor;setting, by the second output driver, the second output signal equal tozero when the control signal indicates the lower power mode; setting, bythe second output driver, the second output signal to be substantiallyequal to a 180-degree-phase-shifted version of the first output signalwhen the control signal indicates the high power mode; combining, by aprimary coil and first matching network residing in-series between thefirst and second output drivers, the first and second output signals togenerate a primary voltage equal to a voltage of the first output signalwhen the control signal indicates the low power mode and twice thevoltage of the first output signal when the control signal indicates thehigh power mode; and generating, by a secondary coil inductively coupledto the primary coil and a second matching network in-series with thesecondary coil, the power signal based on the primary voltage, the powersignal having a first power level when the control signal indicates thelow power mode and a second power level equal to four times the firstpower level when the control signal indicates the high power mode. 2.The method of claim 1, further comprising transmitting said power signalto said implantable device.
 3. The method of claim 1, wherein said firstoutput signal comprises an amplified replica of said first input signaland wherein said second output signal comprises an amplified replica ofa substantially 180-degree-phase-shifted version of said first inputsignal.
 4. The method of claim 1, wherein said implantable devicecomprises a cochlear stimulator.
 5. The method of claim 1, wherein saidinput signal comprises a data signal modulated with a carrier signal. 6.The method of claim 1, wherein the setting of the second output signalequal to zero comprises setting the second output signal equal toground.
 7. The method of claim 1, wherein the first input signalcomprises a periodic square wave.
 8. The method of claim 1, wherein thefirst output signal comprises a first push-pull output signal andwherein the second output signal comprises a second push-pull outputsignal substantially equal to a 180-degree-phase-shifted version of thefirst push-pull output signal.
 9. The method of claim 1, wherein saidimplantable device is an implantable cochlear stimulator.
 10. A systemfor providing a power signal to an implantable device, said systemcomprising: a first output driver configured to receive a first inputsignal and generate a first output signal based on the first inputsignal; a second output driver configured to generate a second outputsignal; a processor connected to an input of the second output driver,configured to receive a control signal that selectively indicates one ofa low power mode and a high power mode, and generate an output signalbased on the control signal that causes the second output driver to setthe second output signal to zero when the control signal indicates thelower power mode and the second output signal to be substantially equalto a 180-degree-phase-shifted version of the first output signal whenthe control signal indicates the high power mode; a first matchingnetwork and a primary coil residing in-series between the first andsecond output drivers, the first matching network and the primary coilbeing configured to combine the first and second output signals togenerate a primary voltage equal to a voltage of the first output signalwhen the control signal indicates the low power mode and twice thevoltage of the first output signal when the control signal indicates thehigh power mode; and a secondary coil inductively coupled to the primarycoil and in-series with a second matching network, the secondary coiland second matching network being configured to generate the powersignal based on the primary voltage, the power signal having a firstpower level when the control signal indicates the low power mode and asecond power level equal to four times the first power level when thecontrol signal indicates the high power mode.
 11. The system of claim10, further comprising a transmitting coil coupled to the secondmatching circuit and configured to transmit said power signal to saidimplantable device.
 12. The system of claim 10, wherein said firstoutput signal comprises an amplified replica of said first input signaland wherein said second output signal comprises an amplified replica ofa substantially 180-degree-phase-shifted version of said first inputsignal.
 13. The system of claim 10, wherein each of said output driverscomprises a number of in-series inverter stages.
 14. The system of claim10, wherein said implantable device comprises a cochlear stimulator. 15.The system of claim 10, wherein the first input signal comprises aperiodic square wave.
 16. The system of claim 10, wherein the firstoutput signal comprises a first push-pull output signal and wherein thesecond output signal comprises a second push-pull output signalsubstantially equal to a 180-degree-phase-shifted version of the firstpush-pull output signal.
 17. The system of claim 10, wherein saidimplantable device is an implantable cochlear stimulator.